|Publication number||US6506025 B1|
|Application number||US 09/557,277|
|Publication date||Jan 14, 2003|
|Filing date||Apr 24, 2000|
|Priority date||Jun 23, 1999|
|Also published as||EP1105646A1, US6582208, US7033132, US20020044867, US20040136846, WO2000079129A1|
|Publication number||09557277, 557277, US 6506025 B1, US 6506025B1, US-B1-6506025, US6506025 B1, US6506025B1|
|Original Assignee||California Institute Of Technology|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (14), Referenced by (49), Classifications (24), Legal Events (6)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application claims the benefit of the U.S. Provisional Application No. 60/140,897, filed on Jun. 23, 1999.
The present application relates to a pump which is formed of rotating parts, which can operate without blades.
Rotating pumps often use blades or propellers to press a fluid in a desired direction. These blades can subject the liquids to harsh impact.
For instance, if the pump is used to pump blood, then the blades can actually cut or otherwise damage certain blood cells, resulting in hemalysis injuring the blood. In other cases, the blades can cause cavitation and produce undesired gas bubble turbulence in the fluid.
The present application teaches a bladeless pump for fluid flow. While the pump has many different applications, one application of the pump is for use in pumping blood and other multiphase flows of body fluids. Other uses include thrust generation and propulsion.
One aspect of the application discloses a pump with a moving part that has a substantially smooth outer surface.
Other aspects include that outer surface having a substantially constant outer diameter. The moving part can be a rotating shaft held captive within an outer cylinder. The inside surface of the outer cylinder includes ridges thereon which are tilted a specified angle. The optimum angle is believed to be 45 degrees. However, any angle a, between (0<a>90 degrees) can produce a pumping effect.
A specified relatively small distance is maintained between the rotating substantially smooth inner surface, and the inside of the outer shell. This small distance can preferably be an amount that prevents substantial leakage of fluid between the ridges.
These and other aspects will now be described in detail with respect to the accompanying drawings, wherein:
FIGS. 1-3 show different views of the pump from different angles;
FIGS. 4A and 4B show flexible pumps; and
FIG. 5 shows a propulsion system.
FIGS. 1 through 3 show different views of the pump of this embodiment. The pump is formed of two coaxial cylinders, one rotating within the other. An outer cylindrical housing 100 includes an outer surface 102 which can be of any desired size or shape. The inner surface 104 of the outer housing is formed with spirally-patterned grooves 106 thereon. The central axis 110 of the outer housing 100 defines a direction of fluid pumping.
A fluid pumping element 120 is located coaxially with the central axis 110. The fluid pumping element 120 has a substantially smooth outer surface 122. It preferably has no blades thereon. Blades, as that term is used herein, are sharp edged objects, such as the usual fan-shaped parts that are used in a pump.
In one embodiment, the fluid pumping element 120 is cylindrical and has a substantially constant outer diameter over its entire active surface. That constant outer diameter can be constant within 1 to 5 percent. The fluid pumping element can be a solid element, or can be a hollow element, such as a tube.
The pumping is held rotatably at its two ends by a first shaft holder 130 and a second shaft holder 140. The shaft can rotate within the first and second shaft holders. An electric motor 150 can provide rotational force to the end.
The chamber surface, formed by inner surface of the outer shell includes a plurality of grooves thereon. The inner surface can have a diameter of ID, which can range rom sizes for operation to pump microfluidics ranging to a size for submarine propulsion. The grooves are ranted at a specified angle. Each of the grooves extends inward from the inner surface by a depth proportional to (OD-ID). The grooves are canted in the direction of desired rotation of the central shaft and in the direction of desired pumping. The pumping element can be rotated in the opposite direction to pump the fluid in the opposite direction.
The inner element, here smooth inner cylinder 120 preferably has an outer diameter of ID-2g, where g is the gap between the inner cylinder and the inner surface. The cylinder can also have smooth nose and ramp portions.
In operation, the central shaft is rotated in the specified direction at a specified rpm rate, e.g. between 5,000 and 20,000 rpm. A shearing force is produced proportional to the angular velocity of the inner cylinder diameter of the inner cylinder. The momentum is transferred to the rest of the fluid. This causes a laminar or turbulent flow around the shaft and along the shaft/groove axis. The viscose or turbulent shear flow eventually extends outward to the grooves.
The angular momentum of the fluid in the grooves has a vector component along its axis, forcing the fluid to move.
The grooves are preferably spaced by a maximum distance of one quarter the shaft diameter. However, there is no minimum effective minimum distance for the groove spacing. A typical groove pattern is usually canted by approximately 45 degrees relative to the direction of the central axis.
In operation, when the shaft spins, it causes a shearing laminar or turbulent flow around the shaft, thereby causing the fluid to flow outward. The shaft is close enough to the grooves to cause fluid flow in the grooves, and to prevent substantial leakage between the grooves.
The grooves facilitate the fluid flow movement. A particularly advantageous use of this pump is in blood flow. A known shear thinning effect in blood causes the red cells to avoid the high shear regions. The cells distance themselves from the high speed-rotating shaft and leave the plasma near the rotating shaft. This process does not occur instantaneously. However, in this pump, the approaching red blood cells feel the stagnation region of the smooth-surfaced rotating shaft. They cells then start an avoidance process with enough lead-time on a viscose time scale to avoid intersecting the path. Previous pumps that rely on the displacement action of the blades at high angular frequencies and speeds often do not leave enough response time for the red blood cells to avoid impact, and its subsequent damaging effects.
The present application pumps the red blood cells without using blades. Hence, there are no blades to cut into blood cells. The shear thinning effect causes the cells to stay away from the high shear portions. The grooves that are used can also be rounded to minimize any damage that could be caused to the blood cells by those grooves.
Many modifications are possible. As disclosed above, the device can be made in a number of different sizes, and the internal ridges can have a number of different sizes and shapes. The area between the internal ridges can be either edged or smooth.
The central shaft is preferably a constant diameter cylindrical rod. However, the shaft can alternatively be a varied diameter cylindrical rod or any other element that is smooth and does not include sharp edges thereon. For example, the cylindrical rod could be formed with an outer surface that has bumps that rounded edges.
The way that the pump works allows other advantages. No sharp corner blades are used. Hence, the whole assembly can be made with flexible materials. One embodiment shown in FIG. 4 uses flexible tube 400 with inner grooves 405. A flexible cylindrical shaft or rod 410 rotates within the outer tube. This can be used for applications where local suction or blowing in complex inner cavities would be required. Another alternative shown in FIG. 4B forms the inner rotating part 400 from a flexible material; so that it can be bent at the area 450 to attach the driving motor.
A rotary motor 450 or any other kind of motor can carry out the rotation of any of these embodiments. One embodiment uses a magnetic levitation pump principle. According to this embodiment, the central shaft is made of a magnetic material. An external coil will generates magnetic field, and the external magnetic field causes the internal cylinder to rotate. The rotating cylinder causes the fluid flow as described above.
One embodiment is for use in propulsion, e.g., as a motor to drive a water vehicle such as a submarine. This embodiment is shown in FIG. 5 with two propulsion pumps 500, 510 with rotating elements 502, 512 that rotate in opposite directions 504, 514. The cylinders have oppositely canted ridges 506, 510 so that they both pump in the same direction. This allows balance in the thrust generation. A control element 520 enables setting the rotating speed of each element individually. The thrust vector, caused when one of these moves faster than the other, can be used for maneuvering. For example, the left side pump part 500 can be initiated to pump faster than the right side pump part 510 to move in a more rightward direction.
This system has advantages when used for propulsion, e.g. thrust generation. The resulting system can be relatively quiet, since no blades cut the water.
This system also has advantages when used for pumping other materials that should not be damaged, besides blood. For instance, since an embodiment can be used which has no moving edges, this system can be used for pumping live aquatic animals or other damageable materials.
Other modifications are contemplated.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3017848||Nov 14, 1960||Jan 23, 1962||Charles R Bishop||Boat propulsion unit|
|US3712754 *||Dec 3, 1970||Jan 23, 1973||Philips Corp||Dosing device|
|US3738773||Oct 20, 1971||Jun 12, 1973||Tait Mfg Co||Bladeless pump impeller|
|US3794449 *||Aug 23, 1972||Feb 26, 1974||Philips Corp||Viscosity pump|
|US3977976||Aug 5, 1974||Aug 31, 1976||Spaan Josef A E||Apparatus for exchange of substances between two media on opposite sides of a membrane|
|US5088899||Nov 9, 1990||Feb 18, 1992||Arthur Pfeiffer Vakuumtechnik Wetzlar Gmbh||Pump with drive motor|
|US5211546 *||May 11, 1992||May 18, 1993||Nu-Tech Industries, Inc.||Axial flow blood pump with hydrodynamically suspended rotor|
|US5254248||Jun 26, 1991||Oct 19, 1993||Terumo Kabushiki Kaisha||Blood plasma separating apparatus|
|US5507629||Jun 17, 1994||Apr 16, 1996||Jarvik; Robert||Artificial hearts with permanent magnet bearings|
|US5685700 *||Jun 1, 1995||Nov 11, 1997||Advanced Bionics, Inc.||Bearing and seal-free blood pump|
|US5900142||Sep 30, 1997||May 4, 1999||Maloney, Jr.; James V.||Mass and thermal transfer means for use in heart lung machines, dialyzers, and other applications|
|US5911685 *||Apr 2, 1997||Jun 15, 1999||Guidant Corporation||Method and apparatus for cardiac blood flow assistance|
|US6234772 *||Apr 28, 1999||May 22, 2001||Kriton Medical, Inc.||Rotary blood pump|
|US6368083 *||Oct 13, 2000||Apr 9, 2002||Kriton Medical, Inc.||Sealless rotary blood pump|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7118353 *||Jun 18, 2003||Oct 10, 2006||Matsushita Electric Industrial Co., Ltd.||Fluid transport system and method therefor|
|US7163385||Mar 4, 2003||Jan 16, 2007||California Institute Of Technology||Hydroimpedance pump|
|US7192244||Jan 6, 2005||Mar 20, 2007||Grande Iii Salvatore F||Bladeless conical radial turbine and method|
|US7398818||Dec 27, 2005||Jul 15, 2008||California Institute Of Technology||Fluidic pump for heat management|
|US7749152||Jan 9, 2006||Jul 6, 2010||California Institute Of Technology||Impedance pump used in bypass grafts|
|US7883325||Mar 24, 2006||Feb 8, 2011||Arash Kheradvar||Helically actuated positive-displacement pump and method|
|US7998190||Apr 21, 2003||Aug 16, 2011||California Institute Of Technology||Intravascular miniature stent pump|
|US8092365||Jan 8, 2007||Jan 10, 2012||California Institute Of Technology||Resonant multilayered impedance pump|
|US8197122||Apr 13, 2009||Jun 12, 2012||Tyco Healthcare Group Lp||Dynamic mixing applicator|
|US8197234||May 24, 2005||Jun 12, 2012||California Institute Of Technology||In-line actuator for electromagnetic operation|
|US8794937||Feb 7, 2011||Aug 5, 2014||California Institute Of Technology||Helically actuated positive-displacement pump and method|
|US8900060||Apr 29, 2010||Dec 2, 2014||Ecp Entwicklungsgesellschaft Mbh||Shaft arrangement having a shaft which extends within a fluid-filled casing|
|US8926492||Apr 30, 2014||Jan 6, 2015||Ecp Entwicklungsgesellschaft Mbh||Housing for a functional element|
|US8932141||Oct 22, 2010||Jan 13, 2015||Ecp Entwicklungsgesellschaft Mbh||Flexible shaft arrangement|
|US8944748||Apr 29, 2010||Feb 3, 2015||Ecp Entwicklungsgesellschaft Mbh||Fluid pump changeable in diameter, in particular for medical application|
|US8979493||Mar 18, 2010||Mar 17, 2015||ECP Entwicklungsgesellscaft mbH||Fluid pump|
|US8998792||May 12, 2014||Apr 7, 2015||Ecp Entwicklungsgesellschaft Mbh||Fluid pump with a rotor|
|US9028216||Sep 22, 2010||May 12, 2015||Ecp Entwicklungsgesellschaft Mbh||Rotor for an axial flow pump for conveying a fluid|
|US9067006||Jun 25, 2010||Jun 30, 2015||Ecp Entwicklungsgesellschaft Mbh||Compressible and expandable blade for a fluid pump|
|US9089634||Sep 22, 2010||Jul 28, 2015||Ecp Entwicklungsgesellschaft Mbh||Fluid pump having at least one impeller blade and a support device|
|US9089670||Feb 3, 2010||Jul 28, 2015||Ecp Entwicklungsgesellschaft Mbh||Catheter device having a catheter and an actuation device|
|US9125655||Jul 18, 2011||Sep 8, 2015||California Institute Of Technology||Correction and optimization of wave reflection in blood vessels|
|US9217442||Mar 2, 2011||Dec 22, 2015||Ecp Entwicklungsgesellschaft Mbh||Pump or rotary cutter for operation in a fluid|
|US9314558||Dec 23, 2010||Apr 19, 2016||Ecp Entwicklungsgesellschaft Mbh||Conveying blades for a compressible rotor|
|US9328741||May 16, 2011||May 3, 2016||Ecp Entwicklungsgesellschaft Mbh||Pump arrangement|
|US9339596||Dec 23, 2010||May 17, 2016||Ecp Entwicklungsgesellschaft Mbh||Radially compressible and expandable rotor for a fluid pump|
|US9358330||Dec 23, 2010||Jun 7, 2016||Ecp Entwicklungsgesellschaft Mbh||Pump device having a detection device|
|US9404505||Mar 4, 2015||Aug 2, 2016||Ecp Entwicklungsgesellschaft Mbh||Fluid pump with a rotor|
|US9416783||Sep 22, 2010||Aug 16, 2016||Ecp Entwicklungsgellschaft Mbh||Compressible rotor for a fluid pump|
|US9416791||Jan 25, 2011||Aug 16, 2016||Ecp Entwicklungsgesellschaft Mbh||Fluid pump having a radially compressible rotor|
|US9512839||Dec 19, 2014||Dec 6, 2016||Ecp Entwicklungsgesellschaft Mbh||Fluid pump changeable in diameter, in particular for medical application|
|US9603983||Oct 22, 2010||Mar 28, 2017||Ecp Entwicklungsgesellschaft Mbh||Catheter pump arrangement and flexible shaft arrangement having a core|
|US9611743||Jul 1, 2011||Apr 4, 2017||Ecp Entwicklungsgesellschaft Mbh||Radially compressible and expandable rotor for a pump having an impeller blade|
|US9649475||Jul 23, 2015||May 16, 2017||Ecp Entwicklungsgesellschaft Mbh||Catheter device having a catheter and an actuation device|
|US9656009||Jul 11, 2008||May 23, 2017||California Institute Of Technology||Cardiac assist system using helical arrangement of contractile bands and helically-twisting cardiac assist device|
|US20030233143 *||Apr 21, 2003||Dec 18, 2003||Morteza Gharib||Intravascular miniature stent pump|
|US20040033153 *||Jun 18, 2003||Feb 19, 2004||Teruo Maruyama||Fluid transport system and method therefor|
|US20040101414 *||Mar 4, 2003||May 27, 2004||Morteza Gharib||Hydroimpedance pump|
|US20050214109 *||Jan 6, 2005||Sep 29, 2005||Grande Salvatore F Iii||Bladeless conical radial turbine and method|
|US20050275494 *||May 24, 2005||Dec 15, 2005||Morteza Gharib||In-line actuator for electromagnetic operation|
|US20060196642 *||Dec 27, 2005||Sep 7, 2006||Morteza Gharib||Fluidic pump for heat management|
|US20060216173 *||Mar 24, 2006||Sep 28, 2006||Arash Kheradvar||Helically actuated positive-displacement pump and method|
|US20070038016 *||Jan 9, 2006||Feb 15, 2007||Morteza Gharib||Impedance pump used in bypass grafts|
|US20070177997 *||Jan 8, 2007||Aug 2, 2007||Morteza Gharib||Resonant Multilayered Impedance Pump|
|US20080267005 *||Apr 24, 2007||Oct 30, 2008||Tyco Healthcare Group Lp||Applicator system and method of use|
|US20090072545 *||Jun 24, 2008||Mar 19, 2009||Van Michaels Christopher||Process of processes for radical solution of the air pollution and the global warming, based on the discovery of the bezentropic thermomechanics and eco fuels through bezentropic electricity|
|US20090268546 *||Apr 13, 2009||Oct 29, 2009||Jon Reinprecht||Dynamic mixing applicator|
|US20100241213 *||May 25, 2010||Sep 23, 2010||California Institute Of Technology||Impedance Pump Used in Bypass Grafts|
|US20140328666 *||Oct 31, 2013||Nov 6, 2014||Diana Michaels Christopher||Bezentropic Bladeless Turbine|
|U.S. Classification||417/53, 604/153, 417/423.1, 604/151, 604/152|
|International Classification||F04D29/18, F04D3/00, A61M1/10, B63H11/08, F04D29/52|
|Cooperative Classification||Y10S415/90, F04D3/00, A61M1/101, F04D29/181, B63H2011/081, F04D29/528, B63H11/08, A61M1/1031, A61M1/1015|
|European Classification||B63H11/08, A61M1/10C, F04D3/00, F04D29/18A, F04D29/52P|
|Oct 2, 2000||AS||Assignment|
Owner name: CALIFORNIA INSTITUTE OF TECHNOLOGY, CALIFORNIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:GHARIB, MORTEZA;REEL/FRAME:011144/0730
Effective date: 20000828
|Jun 30, 2006||FPAY||Fee payment|
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|Jun 16, 2010||FPAY||Fee payment|
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|Aug 22, 2014||REMI||Maintenance fee reminder mailed|
|Oct 14, 2014||FPAY||Fee payment|
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|Oct 14, 2014||SULP||Surcharge for late payment|
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